Synthetic microfluidic systems for hypoxia

ABSTRACT

A cell culture device can include: an internal chamber configured for an internal cell culture that has at least one port coupled to a perfusion modulating device capable of modulating perfusion in the internal chamber; at least one fluid channel bordering the internal chamber that is configured for a channel cell culture that has at least one port coupled to a perfusion modulating device capable of modulating perfusion in the fluid channel; and a wall separating the internal chamber and at least one fluid channel having gaps that fluidly couple the internal chamber with the at least one fluid channel, wherein the perfusion modulating device causes reduced fluid flow. The internal chamber can include a first cell type and the at least one fluid channel includes a second cell type. The first cell type has an ischemic zone in the middle, a non-ischemic zone adjacent with the at least one fluid channel, and a border zone between the ischemic zone and non-ischemic zone. In one aspect, the internal chamber and at least one fluid channel are modeled from physiological features. In one aspect, the internal chamber and at least one fluid channel are modeled from idealized features.

CROSS-REFERENCE

This patent application claims priority to U.S. Provisional ApplicationNo. 61/775,158 filed Mar. 8, 2013, which provisional application isincorporated herein by specific reference in its entirety.

BACKGROUND

Ischemia and hypoxia are common in several pathological conditions, suchas cancer, stroke, acute renal failure, and myocardial infarction.Myocardial infarction occurs when the blood supply from a coronaryartery is occluded leading to reduced supply (e.g., ischemia) thatresults in hypoxia to portions of the myocardium. This blockage of theblood flow and oxygen supply is primarily due to an atherosclerosisplaque leading to partial or complete occlusion of the vessel andsubsequent myocardial ischemia. Total occlusion of the vessel for morethan 4-6 hours results in irreversible myocardial necrosis, butreperfusion within this period can salvage the myocardium and reducemorbidity and mortality. Following an ischemic attack, a series ofresponse mechanisms in the heart, neural, hormonal systems, andvasculature are activated which though initially for beneficial purposescan contribute to worsening of the symptoms and eventual death.

Most of the models of in vivo myocardial ischemia use rodents. In themost commonly used experimental model, the left anterior descendingcoronary artery commonly called as LADA is ligated. This causesreduction in blood flow and subsequent ischemia. Fluorescent imaging isthen used to visualize the vessels. For example, CD31 staining is usedto visualize anatomic vessels and DiOC7 is used to visualize perfusion.Finally tissue hypoxia is quantified with EF5, a nitroheterocycliccompound that has been shown to form adducts at a much higher rate inhypoxic tissue. Even though the animal experiments provide detailedrepresentation following ischemia, these experiments are expensive,technically complex and need to overcome ethical concerns.

In this regard, in vitro models were developed to study the effect ofischemia on cultured cardiomyocytes. These models range from treatingcells to oxygen deprived media, elevated carbon dioxide levels, reducednutrient media (absence of serum, etc.), and finally waste accumulation.Common methods rely on altering the cellular metabolism with a chemicalagent (e.g., cyanide, azide, Antimycin A, etc.) or altering the externalcellular environment by changing gas compositions which is achieved bychanges in temperature and rate of change of fresh media. Currently,ischemia studies on myocytes cultured in vitro use one of the followingtwo methods. In the first method, myocytes are cultured in a 35 mm Petridish. When the cells are nearing confluency, a round glass coverslip isplaced over part of the myocyte monolayer surface to restrict nutrientsupply and gas diffusion. This rapidly decreases intracellular pH andproduces three distinct zones within the monolayer called the ischemiczone (e.g., where the cells don't have access to fresh media and wastemetabolites are present in excess), the border zone (e.g., partial cellsexperience excess waste metabolites and hypoxia whereas the other halfof cells are viable), and finally the non-ischemic zone, where the cellshave abundant supply of fresh nutrients. A less popular method calledthe picochamber system can be used to study ischemic conditions on asingle cell where the cellular microenvironment oxygen is altered by anargon stream parallel to the surface.

However, all of these models have limitations. Therefore, it would beadvantageous to have devices and methods that provide for improvedexperimental analysis and studies on cells and cultures under ischemicand hypoxic conditions.

BRIEF DESCRIPTION OF THE FIGURES

The foregoing and following information as well as other features ofthis disclosure will become more fully apparent from the followingdescription and appended claims, taken in conjunction with theaccompanying drawings. Understanding that these drawings depict onlyseveral embodiments in accordance with the disclosure and are,therefore, not to be considered limiting of its scope, the disclosurewill be described with additional specificity and detail through use ofthe accompanying drawings.

FIG. 1A illustrates an embodiment of a device for use in ischemia andhypoxia assays.

FIG. 1B illustrates a representation of ischemia zones in the centralchamber of the device.

FIG. 2A illustrates an embodiment of a device having a central chamberand fluid channels that are modeled from physiological features.

FIG. 2B illustrates a magnification of a wall separating the centralchamber and fluid channels.

FIG. 2C illustrates an embodiment of a device having multiple channels.

FIG. 3A illustrates an embodiment of an idealized device having acentral chamber and fluid channels that are idealized.

FIG. 3B illustrates an embodiment of a circular device having a centralchamber and fluid channels that are idealized.

FIG. 3C illustrates an embodiment of a circular device having a centralchamber and multiple fluid channels that are idealized.

FIG. 4 illustrates an embodiment of manufacturing the device.

FIG. 5 illustrates fluid flow dynamics with posts that can be used aswalls between the chamber and channels.

FIG. 6 illustrates an embodiment of a wall with slits that can separatetwo different channels in the device.

DETAILED DESCRIPTION

In the following detailed description, reference is made to theaccompanying drawings, which form a part hereof. In the drawings,similar symbols typically identify similar components, unless contextdictates otherwise. The illustrative embodiments described in thedetailed description, drawings, and claims are not meant to be limiting.Other embodiments may be utilized, and other changes may be made,without departing from the spirit or scope of the subject matterpresented herein. It will be readily understood that the aspects of thepresent disclosure, as generally described herein, and illustrated inthe figures, can be arranged, substituted, combined, separated, anddesigned in a wide variety of different configurations, all of which areexplicitly contemplated herein.

Generally, the present invention includes a microfluidic device andassay for studying ischemia and hypoxia on cells in controlled perfusionconditions. The microfluidic device can induce ischemia and hypoxia byinterrupting the flow of media and oxygen to cells in the microfluidicdevice. The device can selectively block the flow of oxygen or fluidshaving oxygen from the cells in the device, which simulates blockingblood vessels supplying oxygen to tissue to provide a hypoxic condition.The resulting restriction of flow causes an oxygen shortage in the cellsin the device, which can lead to necrosis in portions of the cells, cellculture, or tissue area in the device. The device can be used for acontrolled study of ischemia and hypoxia and the impact on cells in thedevice, which can be extrapolated for understanding ischemia andhypoxia. The device can also be used for development of new therapeuticsfor treating ischemia and hypoxia affected tissues in a subject.

The device can be configured for high throughput assays used forstudying any cell having ischemia or hypoxia. The device can havephysiological realistic features, such as tissue chambers and vesselflow paths, which is referred to as a synthetic microvascular network(SMN). The device can have idealistic features, such as straight flowpaths and regular shaped tissue chambers, which is referred to as anidealized microvascular network. SMN and IMN are known terms in the art.For example, the device can provide a platform for studying myocardialischemia (MI) in a physiological microenvironment (e.g., SMNenvironment). MI occurs when the blood supply to portions of the heartis interrupted, which can be simulated by interrupting the flow of cellculture media, oxygen or oxygen-containing fluid to the cells in thedevice. The device may include means for inhibiting the supply of mediaand/or oxygen to the cells. For example, the device can be used tosimulate blockage of a coronary artery following the rupture of anatherosclerotic plaque. The reduced flow of media (e.g., simulated bloodsupply) can simulate ischemia, and the nutrient shortage can lead tomyocardial necrosis, which can cause contractile dysfunction and hinderthe ability of the heart to perfuse vital organs necessary for survival.The same technique can be used to inhibit oxygen and induce hypoxia. Theexample presented here is based on myocytes. However, the device can useother cells to study ischemia and hypoxia in other tissues e.g.,neurons, nephrons, or hepatocytes.

The device can be configured to provide an in vitro model to reproduceas many anatomical, physiological and biochemical aspects as possible ofthe in vivo features, in order to be functional and accurate. As such,the device can include a microenvironment with a central chamber havingmyocytes surrounded by a network of capillary channels in the device forproviding nutrients to the central chamber. The shape of the centralchamber and capillary network can be shaped similar to anatomicalexamples, which can be irregular and non-linear and referred to assynthetic microvascular networks (SMN). Alternatively, the shape of thecentral chamber and capillary network can be shaped in an idealizedformat with straight channels with regular and linear features, which isreferred to as an idealized microvascular network (IMN). As such, themicrofluidic device can be configured to mimic the microenvironment oftissue cells in a complex network of capillaries. Fluid flow (e.g.,simulated blood flow and/or oxygen flow) in these capillary channelssurrounding the central chamber can be readily switched on and off tosimulate ischemia induced conditions and hypoxia. Cultured endothelialcells in the capillaries surrounding the central chamber (e.g., myocyteculture) enable studies on interaction between endothelial cells andtissue (e.g., myocardium). However, other cells can be used besidesmyocytes for studying other tissue types.

FIG. 1A illustrates an embodiment of a microfluidic device 100 inaccordance with the present invention. As shown, the device includes abody 102 that defines an internal chamber 110 surrounded by a capillarychannel 120. The internal chamber has a flow inlet 112 and a flow outlet114. The capillary channel 120 has a capillary inlet 122 and a capillaryoutlet 124. The internal chamber 110 and capillary channel 120 areseparated by posts 130 with gaps 132 between the posts 130.

The capillary channel 120 can be a fluid flow channel and the internalchamber 110 can be a tissue space. The capillary channel 120 andinternal chamber can be linear elements or idealized (IMN) or non-linearelements or synthetic (SMN). FIG. 1A illustrates an IMN.

One embodiment of a synthetic microvascular network (SMN) 12 can includerealistic flow paths and tissue spaces, as shown in FIG. 2A-2B. Thecapillary network is irregular. Here, the wall of a flow channel (e.g.,capillary channel) separating the flow channel lumen from the lumen ofthe tissue space 13 is shown in detail to show the pillars 15 a and gaps15 b. In this embodiment, one wall of the nonlinear flow channel 14 isconstructed such that portions of the wall contain gaps 15 b locatedbetween portions of the wall, called pillars 15 a (or posts, islands,etc.), which may be configured to provide gaps 15 b of various selectedsizes. For fabrication of the SMN 12 comprising the extravascular(extra-flow channel) tissue space 13, CAD drawings of a physiologicalnetwork are modified to include gaps 15 b with desired gaps or pores inthe walls of the vessels. The patterns of these vessels include tissuesections comprising a portion of or the entire physiological tissuespace. The lumens of the tissue spaces shown in FIGS. 2A and 2B maycomprise posts, pillars, or other structures made of plastic substrateto facilitate the growth of adhesion-dependent cells.

FIG. 6 shows that two capillary channels can be separated by a wallhaving 50 micron-wide slits. As such, the devices can include centralchambers surrounded by at least two adjacent capillary channels. In viewof the SMN of FIGS. 2A and 2B, a corresponding SMN modeled after livephysiology with at least two capillary channels would look like FIG. 2C.FIG. 2C illustrates an embodiment of SMN network having SMN fluidpathways and SMN multi-chambered cell culture constructs.

FIG. 2C illustrates a SMN 10 having one of more fluid inlets In 9 andone or more fluid outlets Out 9 with one or more multi-channelconstructs 1, 2, 3, 4, each having a central chamber 8 a, 8 b, 8 c, 8 d(e.g., while four multi-chamber constructs are shown, any integer can beused). The multi-chamber constructs 1, 2, 3, 4 can be configured withinlets and outlets in accordance with any of the embodiments or figuresdescribed herein. Also, while shown to be SMN, the configuration can bean IMN. The SMN can be configured with any number of fluid pathways 7linking the multi-channel constructs, which can be in any manner, andwhich SMN can be designed via simulation of real biological orartificial fluid pathways.

As shown, multi-channel construct 1 can include a central chamber 8 asurrounded by an outer conduit layer 1 a (e.g., outer capillary channel)with barrier layer channels 1 b, 1 c therebetween. The outer conduitlayer 1 a can be fluidly coupled with an inlet In 9 and an outlet Out 9.Also, the outer conduit layer 1 a can include an inlet In 1 a and anoutlet Out 1 a. The barrier layer channels 1 b, 1 c, can include inletsIn 1 b, In 1 c and outlets Out 1 b, Out 1 c, respectively. While notshown, the central chamber 8 a can include inlets or outlets, or it canreceive content from the barrier layer channel 1 c.

As shown, multi-channel construct 2 can include a central chamber 8 bsurrounded by an outer conduit layer 2 a (e.g., capillary channel) withbarrier layer channels 2 b, 2 c therebetween. The outer conduit layer 2a can be fluidly coupled with an inlet In 9 and an outlet Out 9. Also,the outer conduit layer 2 a can include an inlet In 2 a and an outletOut 2 a. The barrier layer channels 2 b, 2 c, can include inlets In 2 b,In 2 c and outlets Out 2 b, Out 2 c, respectively. While not shown, thecentral chamber 8 b can include inlets or outlets, or it can receivecontent from the barrier layer channel 2 c.

As shown, multi-channel construct 3 can include a central chamber 8 csurrounded by an outer conduit layer 3 a (e.g., outer capillary channel)with barrier layer channels 3 b, 3 c therebetween. The outer conduitlayer 3 a can be fluidly coupled with an inlet In 9 and an outlet Out 9.Also, the outer conduit layer 3 a can include an inlet In 3 a and anoutlet Out 3 a. The barrier layer channels 3 b, 3 c, can include inletsIn 3 b, In 3 c and outlets Out 3 b, Out 3 c, respectively. While notshown, the central chamber 8 a can include inlets or outlets, or it canreceive content from the barrier layer channel 3 c.

As shown, multi-channel construct 4 can include a central chamber 8 dsurrounded by an outer conduit layer 4 a with barrier layer channels 4b, 4 c therebetween. The outer conduit layer 4 a can be fluidly coupledwith an inlet In 9 and an outlet Out 9. Also, the outer conduit layer 4a can include an inlet In 4 a and an outlet Out 4 a. The barrier layerchannels 4 b, 4 c, can include inlets In 4 b, In 4 c and outlets Out 4b, Out 4 c, respectively. While not shown, the central chamber 8 d caninclude inlets or outlets, or it can receive content from the barrierlayer channel 4 c.

FIG. 3A shows a portion of an idealized microvascular network IMN 112 ina microfluidic chip. The IMN 112 comprises the idealized extravasculartissue space 13 surrounded by linear flow channels 114. Walls 115separating the tissue space 13 from the linear flow channels 114 arepermeable to aqueous buffers and are formed by plastic structures 115 bseparated by gaps 115 a that range in size from 0.2 μm to 5 μm.Alternatively, the walls 115 may be made liquid permeable by way ofpores in the wall that are from 0.2 μm to 30 μm in diameter. Theextravascular tissue space 13 contains posts 13 a (e.g., pillars)configured to facilitate the growth of adhesion-dependent cells to forma three-dimensional solid mono- or co-tissue culture or tumor. The posts13 a can be included in any vascular fluid flow path or extravascularspace in any of the microfluidic chips. The posts 13 a distribution,amount or arrangement or shape. Also, the tissue space 13 can be devoidof the posts 13 a.

FIG. 3B shows a round IMN 312 in a microfluidic chip. The IMN includes around tissue space 313 surrounded by a barrier space 315, which issurrounded by a wall 317 having gaps 319, and where an outer capillarychannel 321 is on the outside. As shown, the barrier space 315 caninclude posts or pillars for cell culturing tissue.

The embodiments of the device can include a plastic, disposable andoptically clear microfluidic chip containing two distinct sections. Thefirst section includes a central chamber for culture of tissue cellssurrounded by the second section being capillaries of endothelial cells.The device can be created by separating the central chamber (e.g.,tissue chamber or internal chamber) for culture of cells (e.g.,myocytes) from the capillary channels lined with endothelial cells byutilizing posts that mimic membranes. The posts create islands which areseparated by submicron-micron gaps to allow for diffusion based fluidicconnection between the capillary channels and the central chamberleading to a microenvironment observed in vivo with cells (e.g.,myocytes) being surrounded by capillaries.

FIG. 5 shows that multiple pillars be used in the flow direction, whichis from the capillary channels into the central chamber. As such, thewalls can be a series of pillars with gaps and flow space therebetween.

FIG. 3C shows another embodiment of a multi-channel structure 800 inaccordance with the principles of the present invention. Here, the wallsare made of the series of pillars in accordance with FIG. 5. Themulti-channel cell culture device 800 is shown to include an internalchamber 810, an inner boundary layer channel 820, an outer boundarylayer channel 830, and an outer conduit layer channel 840. However, onlyone boundary layer channel or more than two additional boundary layerchannel can be located between the internal chamber 810 and outerconduit layer channel 840. The internal chamber 810 can include a fluidinlet 812 and a fluid outlet 814. The inner boundary layer channel 820can include at least one fluid inlet and at least one fluid outlet asdescribed herein. The outer boundary layer channel 830 can include atleast one fluid inlet and at least one fluid outlet as described herein.The outer conduit layer channel 840 can include at least one fluid inletand at least one fluid outlet as described herein. The internal chamber810 can be defined by a porous tissue chamber wall 816, the innerboundary layer channel 820 can be defined by the porous tissue chamberwall 816 and a porous boundary layer wall 826, the outer boundary layerchannel 830 can be defined by the porous boundary layer wall 826 and aporous outer conduit wall 836, and the outer conduit layer channel 840is defined by the porous outer conduit wall 836 and an external wall 802that is not porous. Here, the porous walls 816, 826, 836 can include aplurality of posts 860 that form the walls with the gaps between theposts 860. The porous walls 816, 826, 836 have one or more posts 860laterally or radially oriented to form the walls.

In one embodiment, any of the chambers/conduits can include structureposts 850 that can be used to provide structure between top walls andbottom walls. The structure posts 850 can be coupled to a bottom wall,and may be coupled to a top wall when integrated with the side walls.Also, the top wall as a lid can rest on the structure posts 850. Thestructure posts can be used for cell culture, and can result in a highercell density for organ simulations. FIG. 3C shows the central chamber810 as having the posts 850, but it can be devoid of posts. Any of theboundary channels 820, 830 can include the posts 850 or be devoid ofposts. The outer channel 840 can include the posts 850 or be devoid ofposts

The device having the internal chamber surrounded by the capillarychannels accurately reproduces the size and flow of a biologicalmicroenvironment, and enables a more physiologically-relevant testingsystem for therapeutic screening, as well as basic research of ischemiaand hypoxia. Advantages in microfluidic technology (e.g.,polydimethylsiloxane or PDMS based device) enable creation of smallvolume, inexpensive, disposable chips having the internal chambersurrounded by the capillary channels. Very thin (e.g., <100 μm) PDMSconstructs can be used to realize long-term cell culture and cellularassays on these microfluidic chips. In one example, by bonding thepolymer microchannel to a custom glass bottom laid out in theappropriate form, the model can be readily extended onto standard wellplates (e.g., 24 well plates), providing a ready method to scale-up tohigh-throughput screening. The device configuration provides the abilityto study differences between healthy and diseased microvasculature ofthe cells (e.g., myocytes).

In one embodiment, the device can provide a microenvironment (e.g.,size, volume, and vasculature) of the cells (e.g., cardiomyocytes) witha network of endothelial cells in the capillary channels surrounding thecells in the internal chamber. The devices configuration allowsperfusion, occlusion, and reperfusion at the flow rates observed in livecapillaries by application to the channels of the device. The deviceconfiguration allows introduction of various insults, chemical (e.g.,test pharmaceuticals) or physical (e.g., ischemia and hypoxia) to thecells in the capillary channels and internal chamber. The devices, whenmade from a transparent material or other optically transmissivematerial, allows for real-time visualization of the assays. The deviceis amenable to high throughput for therapeutic screening assays foragents to treat ischemia and hypoxia.

The device can be fabricated with PDMS using conventional softlithography (see FIG. 4). CAD drawings of the device can be developed toinclude post structures with gaps to act as paths for diffusion of fluid(e.g., nutrients or oxygen) into the central cell chamber. The CADdrawings can also be converted into a computational domain forsimulational analysis. Briefly, the steps involved in the fabricationprocess shown in FIG. 4 include: (a) Spin-coating of photoresist (PR);(b) UV photolithography of the PR; (c) Development of the PR; (d) PDMScasting over developed PR, followed by PDMS curing; and (e) PDMS bondingto a cap (e.g., microscope slides, coverslip, glass, etc.). The devicescan be tested visually for structural and fluidic integrity usingfluorescent dyes. Fabrication of microfluidic devices from PDMS can bemodulated to vary the widths, depths, PDMS concentration and bakingtime.

Additional methods can be used for preparing the devices, such as thefollowing example. The AutoCAD designs can be printed at high resolutionon high-quality chrome masks. The chrome masks can be used for UVpatterning of the desired thickness of positive resist spun on top of asilicon wafer. Silanization via the use of an adhesion promoter(Hexamethyldisilazane, HMDS) can be used to enhance the strength ofbonding of the photoresist to the silicon wafer. Sylgard 184 PDMS (DowCorning, Midland, Mich.) can be poured over developed photoresist togenerate complementary microchannels in PDMS. The PDMS can be cured at60° C. for 4-6 hours in an oven, following which the PDMS will be peeledoff from the master. Through holes, defining the inlets and outlets, canbe punched using a beveled 25-gauge needle. The bonding surfaces of thePDMS and a pre-cleaned (ultrasonicated) glass slide/wafer can be bondedfollowing oxygen plasma treatment. Tygon Microbore tubing with anoutside diameter of 0.03″ and inner diameter of 0.01″ connected to 30gauge stainless steel needle can be used for world-to-chip interfacing.The completed device can be sterilized by autoclaving at 121° C. for 15minutes and stored in sterile environment until usage. The finisheddevices can be tested visually for structural integrity, particularlypaying attention to the post structures. The fluidic integrity of theports and PDMS/glass slide seal can be verified at the operational flowrates.

Various devices configurations can be obtained in accordance with theinvention, with central chamber size ranging from 100 μm to 10 mm,surrounded by capillary channels of width 5 μm to 500 μm and height 5 μmto 500 μm, separated by posts 5 μm to 500 μm with gaps of 500 nm to 50μm. In one example, the device can include a 1 mm central chamber(across) surrounded by 20 μm capillary channels (wide) with a depth of100 μm (height of chamber and channels). The posts separating thechamber from the capillary channels can be 50 μm wide with gaps of 1 μm.FIG. 6 shows an SEM image of two channels joined by ˜50 μm long slitsfabricated in our laboratory with PDMS using conventional softlithography techniques. Also, the gaps can be up to 500 nm. By comparingthe yield and performance of different gap sizes in devices, tradeoffsbetween gap size and performance of ischemia, hypoxia, and myocardialinfarct can be studied in these devices.

In one embodiment, in vitro microfluidic devices can be used to assayfor analysis of MI or other conditions from ischemia and hypoxia. The MIdevice can include a plastic disposable and optically clear microfluidicchip with myocytes fed by an array of capillaries comprising ofendothelial cells. Synchronized contraction of healthy myocytes can bevisualized real-time. Ischemia and hypoxia of varying intensity andduration can be modeled as needed. Effect of both drug based therapiesand recent advances in stem cell therapy can be readily tested in thedevice. The assay can be interfaced with 12-96 well plates (e.g., 24well plates) for medium to high throughput assays, thereby allowinglower reagent cost, rapid turnaround times and increased biochemicalknowledge to yield benefits during therapies. The device can also beused to study targeted therapy for regeneration of myocytes.

The device can include of a microfluidic chip with tissue cells (e.g.,myocytes, neurons, hepatocytes, etc.) fed by an array of capillariescomprising of vascular cells (endothelial cells). Perfusion of tissuecells in the central chamber can be varied in intensity and duration bychanges in the flow rate in the capillaries. The benefits of the devicethat can have varied flow in the channels includes: allow perfusion,occlusion and reperfusion at the rates observed in blood vessels; allowintroduction of various insults (chemical or physical); providereal-time visualization; and perform medium to high throughput fortherapeutic screening assays. This allows the use of the device to rangefrom pharmaceutical companies developing drugs for diseases underischemia and hypoxia, characterize the mechanisms of ischemia andhypoxia to resolve the individual stimuli, and in drug discovery for thedevelopment of regenerative medicine. The device can be used in methodsfor creating ischemia induced hypoxia. The device can be used in methodsfor creating reperfusion injury. The device can be used in methods forcreating gradients of hypoxia. The device can be idealized, or imagedwith vascular and tissue spaces separated by nano to micro gaps. Thedevice can be used in an assay for creation of ischemia induced hypoxiafor cells, such as myocytes, neurons, nephrons, or hepatocytes. Thedevice can be used in an assay for ischemia induced hypoxia withco-culture of cells. The device can be used in an assay to screen forchemical based ischemia. The device can be used in an assay for physical(e.g., mechanical stress) means based ischemia. The device can be usedin an assay to screen for therapeutics on hypoxic cells. The device canbe used to characterize key components (e.g., viability, pH/hypoxia,biomarkers) in ischemia, hypoxia, and post MI using morphologicalanalysis and fluorescent probes.

The device design parameters (e.g., chamber size, capillary perfusionrates and time points) can be optimized from in vivo data followed byco-culture with endothelial cells. Inflammation based injury followingischemia involving leukocyte interactions can also be demonstrated. Thedevice can be integrated to a well plate format to permit higherthroughput. The device can be used in methods to study stem celltherapies for regeneration of the cells (e.g., myocytes) in the centralchamber. The device can be used in methods to study drug basedtherapeutics for cells in the central chamber. Device predictions can becompared with in vivo studies.

A well-controlled system such as the device can enable both drugdiscovery and basic understanding of the phenomena during and post MI.In addition, use of an in vitro model that mimics the physiologicalmicroenvironment of the myocardium can reduce animal studies during thepreliminary stages of the therapeutic development. Thus, the device canreproduce the critical biological characteristics of the MI, therebyproviding a valid and cost-effective tool for studying new therapeuticapproaches.

The invention can provide a microfluidic device that mimics themicroenvironment of myocytes in a complex network of capillaries. Fluidflow (blood flow) in these capillaries can be readily switched on andoff to simulate ischemia induced conditions. Culture of endothelialcells in capillaries beside the myocardium chamber (myocytes) enablesstudies on interaction between endothelial cells. The device can includea plastic, disposable and optically clear microfluidic chip containingtwo distinct sections; a central chamber for culture of myocytessurrounded by capillaries of endothelial cells. The device is created byseparating the central chamber for culture of myocytes from thecapillary channels lined with endothelial cells by a design utilizinglarge posts. The posts create islands which are separated bysubmicron-micron gaps to ensure diffusion based fluidic connectionbetween the capillary channels and the central myocyte chamber leadingto a microenvironment observed in vivo with myocytes being surrounded bycapillaries.

The device can include a reproduction of complex microvascular networksonto plastic (e.g., PDMS) substrates. These networks, originallyrendered from in vivo images of tissues, allow quantitative study ofdrug particle adhesion to and transfection of vascular endothelial cellsin circumstances closely mimicking in vivo conditions. This methodologywas used to create devices from a microvascular network of hamstercremaster muscle in vivo ranging from 15-100 μm. FIG. 2A shows anexample of the complete microvascular network on the microfluidic chipwith a magnified view of microchannels in FIG. 2B.

The device can provide a microenvironment of the cardiomyocytesnourished by a complex network of capillaries and interactions withendothelial cells. The ischemic insult used in the methodologies of theinvention allows for studies on reperfusion effects which are stronglyimplicated in the generation post infarction complications. The devicecan selectively provide for normal and reduced blood flow situationsfound in the infarctions. The device allows introduction of bothchemical and physical insults to the cells.

In one embodiment, a cell culture device can include: an internalchamber configured for an internal cell culture that has at least oneport coupled to a perfusion modulating device capable of modulatingperfusion in the internal chamber; at least one fluid channel borderingthe internal chamber that is configured for a channel cell culture thathas at least one port coupled to a perfusion modulating device capableof modulating perfusion in the fluid channel; and a wall separating theinternal chamber and at least one fluid channel having gaps that fluidlycouple the internal chamber with the at least one fluid channel, whereinthe perfusion modulating device causes reduced fluid flow. In oneaspect, the perfusion modulating device includes a pump. In one aspect,the internal chamber includes a first cell type and the at least onefluid channel includes a second cell type. In one aspect, the first celltype has an ischemic zone in the middle, a non-ischemic zone adjacentwith the at least one fluid channel, and a border zone between theischemic zone and non-ischemic zone. In one aspect, the internal chamberand at least one fluid channel are modeled from physiological features.In one aspect, the internal chamber and at least one fluid channel aremodeled from idealized features.

In one embodiment, a cell culture system can include: the device of oneof the embodiments; and a perfusion modulating device coupled to theport of the internal chamber and/or to the port of the at least onefluidic channel.

In one embodiment, a method of inducing ischemia can include: providingthe device of one of the embodiments having a first cell culture in theinternal chamber and a second cell culture in the at least one fluidchannel; modulating perfusion in the internal chamber with the perfusionmodulating device; and assaying for ischemia in the first cell culture.In one aspect, the method can include modulating perfusion in the atleast one fluid channel. In one aspect, the method can include varyingintensity and duration of fluid flow in the at least one fluid channelso as to vary perfusion in the internal chamber. In one aspect, themethod can include introducing a chemical and/or physical insult to thefirst cell culture in the internal chamber. In one aspect, the methodcan include inducing gradients of hypoxia in the internal chamber. Inone aspect, the method can include inducing hypoxia in myocytes,neurons, nephrons, or hepatocytes in the internal chamber. In oneembodiment, the method can include screening therapeutics on hypoxiccells in the first cell culture in the internal chamber. In oneembodiment, the method can include characterizing viability, pH,hypoxia, or biomarkers in cells in the first cell culture in theinternal chamber. In one embodiment, the method can include regeneratingcells the internal chamber. In one embodiment, the method can includevisualizing cells in the first cell culture in the internal chamber. Inone embodiment, the method can include simulating a myocardial infarctin the first cell culture of myocytes in the internal chamber. In oneembodiment, the method can include inhibiting fluid flow in the internalchamber sufficient to induce low to moderate ischemia. In oneembodiment, the method can include inhibiting fluid flow in the internalchamber and at least one fluid channel sufficient to induced moderate tosevere ischemia.

EXPERIMENTAL

A component useful for mimicking the microenvironment of myocytes is torecreate the 3D matrix conditions found in vivo. In this context thedevice can use Matrigel in the myocyte chamber to create a 3D Matrix.Cardiac myocytes (e.g. from Lonza, Walkersville, Md.) can be cultured incell culture medium. A Matrigel (Kleinman & Martin, 2005) solution canbe introduced into the chamber from the inlet port of the chamber usinga syringe pump and allowed to polymerize for 2 hours. Myocytes at aconcentration of 5×10⁵ cells/ml mixed with matrigel can be injected intothe chamber and incubated at 37° C. and 5% CO2. Flow in the capillariescan be continuous at a shear rate of 15 sec⁻¹ to 500 s⁻¹. Media can bereplaced using the programmable syringe pump (Harvard PHD 2000). Cellviability can be assed using LIVE/DEAD® viability kits (Invitrogen, CA)with green stain indicating healthy cells and red unhealthy and decayingcells.

A wide variety of cells (e.g., endothelial, epithelial, ovarian, breast)can be cultured in the device. However, each cell type may need finetuning of culture protocols for culture in these devices. Seedingdensity of the cells in addition concentration of matrigel can be variedto grow a uniform layer. Finally, media replacement time can beoptimized to overcome any rapid buildup of waste products from thecells.

Measurement of Synchronized Beating and Contraction of Myocytes:

Beating exhibited by cardiac myocytes can be recorded using microscopeconnected to a camera. The procedure can be automated using software(e.g. NIKON Elements) to see if the beating of the myocytes issynchronized. The beats per minute can serve as the baseline forsubsequent ischemia assays.

In order to access whether myocytes have intact contractile properties,electrodes can be inserted in the ports of the chamber and an electricalsignal can be applied. Contraction length and duration can be recordedfor the cells to serve as baseline following ischemia. A plot of % ofcells exhibiting synchronized beating can be used to analyzeexperimental observations. The frequency, voltage and pulse durationbeing used to test the contraction properties can be varied to yield aplot of contraction length for cells.

Myocytes exchange oxygen and nutrients with the blood across themyocyte-capillary boundary. During normal behavior of blood flow,replacement of fresh nutrients keeps the waste products level low, butafter an ischemia, it results in a shock to the myocytes. However, acommon feature is that in the periphery of the ischemic zone, myocytesstill have access to nutrients via capillaries whereas the area awayfrom the capillaries becomes necrotic. The diffusion of the nutrientsfrom the capillary to the center of the ischemic area is dependent onthe consumption rate of the myocytes and the diffusion rate. In order toassess this diffusion the device can perform the following simulationand experiments.

Ischemic conditions can be subsequently generated in the device followedby experimental analysis on pH/hypoxia changes. The device can be usedto assay ischemic myocytes using hypoxia markers; pimonidazole andHIF-1alpha; mitochondria depolarization using Mitotracker probe;inflammation using ICAM-1 and P-selectin; and finally for apoptoticregions using Tunnel and Caspase assays. The device can allow monitoringof the gradients for hypoxia regions using SNARF assays. In allexperiments, the nucleus can be counterstained with Hoechst to monitorintegrity of the cells. LIVE/DEAD® assay can be utilized as needed.

A general-purpose Computational Fluid Dynamics (CFD) code (e.g.,CFD-ACE+), based on the Finite Volume Method (FVM) can be used todiscretize and solve the governing equations for fluid flow anddiffusion in the device. A three-dimensional computational mesh similarto the one shown in FIG. 5 can be generated by importing the AUTOCADlayouts into CFD-GEOM, the grid generation module. The computation-readygeometry and meshes are then loaded into CFD-ACE+ for simulation.Modules of fluid flow and chemistry can be used. Flow rates mimickingthe shear rates observed in capillaries during healthy and ischemicconditions can be simulated. The time taken for the cell culture mediumto diffuse through the entire central chamber can be analyzed. Plot ofdiffusion time versus flow rate can be generated which can provideguidance during the experimental analysis following ischemia, hypoxia,and MI.

Experimental Diffusion in the Myocyte Chamber:

The myocyte chamber and the capillary channels can be primed withphosphate buffer. Fluorescent dye, FITC at a concentration of 1 μM canbe injected into the capillary sections of the network. The diffusionrate of FITC from the capillary channels into the myocyte chamber can berecorded by taking time-lapse images of the device every 5 minutes tillthe chambers are completely filled. A second experiment can be runmimicking the ischemic condition. If the results between the experimentsand simulation match well, one can use subsequent simulation runs asguidance for testing any new flow rates.

Modeling MI in the Developed Device:

A MI model can be provided in the device by ischemic shock for themyocytes. This assay can represent the scenario where blood flow (e.g.,nutrients and oxygen) is hindered to the myocardium. Reperfusion can bestarted and the damage to the cardiac myocytes will be assessed. Changesin pH, upregulation of inflammation markers and viability can bemeasured.

Myocytes exchange oxygen and nutrients with the blood across themyocyte-capillary boundary. In the device, myocytes are initially fed bymedia replacement through the myocyte-capillary interface and themyocyte chamber itself. During normal behavior of blood flow,replacement of fresh nutrients keeps the waste products level low, butafter ischemia, when the supply is limited due to reduced blood flow, itresults in ischemic shock in the myocytes. However, a common featureobserved in MI hearts is that in the periphery of the infarct, themyocytes still have access to nutrients via capillaries whereas the areaaway from the capillaries becomes necrotic. The diffusion of thenutrients from the capillary to the center of the infarct area isdependent on the rate of consumption by the myocytes and the diffusionrate. In order to assess this diffusion one can perform the simulationsand experiments described herein.

Initiation of Ischemic Shock in the Device:

Myocytes can be allowed to grow to confluence in the myocyte chamber to80-90% confluency and synchronized beating. A this stage, mediaperfusion to the myocyte chamber can be stopped completely for 5minutes, 30 minutes, 4 hours and 24 hours, respectively, to modelischemia and hypoxia. Two different conditions can be utilized. In thefirst, flow in the capillary channels can be continued (e.g., mimickinglow ischemic conditions) during the period of media stoppage to themyocyte chamber. In the second set, flow in the capillary channels canalso be stopped (e.g., severe ischemic conditions) for the duration ofthe blockage and switched back on at the respective time points. Atrespective end time points, cell conditions can be assayed forsynchronized beating, intact contraction and viability. Controlexperiments with flow being normal in both the myocyte chamber andcapillary channels can be performed. A plot of distance versus cellswith synchronized beating from the capillary channel to the center ofthe chamber can be generated and compared to controls. Similarly, thereduction in the contractile length and the number of cells can becompared. Morphological analysis of the cells can be conducted usingphase contrast microscopy.

Three distinct regions of ischemia can be induced as shown in FIG. 1A;(a) the ischemic zone where the cells don't have access to fresh mediaand waste metabolites are present in excess specifically for the cellspresent in the center of the chamber, (b) the border zone where partialcells experience excess waste metabolites and hypoxia whereas the otherhalf of cells are viable, and finally (c) non-ischemic zone, where thecells have abundant supply of fresh nutrients near to the capillarychannels.

An example of a method of creating hypoxia is shown in Table 1.

TABLE 1 Example to create Hypoxia Tissue Flow in Condition of ChamberCapillary Time Point Mimicked Flow On On (15 sec-1) 5, 30 minute,Healthy Cells(Control) 4 and 24 hr Flow Off On (15 sec-1) 5, 30 minute,Low Level Ischemia 4 and 24 hr Flow Off On (2.5 sec-1) 5, 30 minute, Lowto moderate 4 and 24 hr Ischemia Flow Off Off and On 5, 30 minute,Moderate Ischemia (15 sec-1) 4 and 24 hr Flow Off Off and On 5, 30minute, Severe Ischemia (2.5 sec-1) 4 and 24 hr

The flow in capillary Off and On implies that the flow in capillarychannel was also stopped during the stoppage of flow in the centralchamber for the respective time points of 5 minutes, 30 minutes, 4 hoursand 24 hours. However, at the end of these time points, flow incapillary channel was turned on and the cells were assayed for viabilityat 24 hour post flow being turned on. This mimics the reperfusionscenario observed in vivo.

One can look at alternative time points for the varying ischemic effectson the myocytes.

Measurement of pH/Hypoxia Changes in the Myocyte Chamber:

Following ischemia, a gradient of hypoxia can be developed as thenutrients are not being replenished fast enough to the myocytes. Thisresults in pH changes in regions of the myocardium or the myocytechamber in the device. In order to access the varying pH/hypoxiaconditions in the myocyte chamber, one can use the fluorescent pHindicator dye SNARF®-4F (Invitrogen, CA) which exhibits a significantpH-dependent emission shift (from yellow-orange to deep redfluorescence) and allows determination of hypoxic regions. The myocytechamber can be injected with SNARF-4F at a concentration of 10 μMdiluted in cell culture media. The entire chamber can be then dividedinto sections using virtual grids. Image analysis can be performed toyield areas with varying levels of pH changes by plotting distance fromcapillary channel versus intensity. The varying pH/hypoxia conditions inthe myocyte chamber can be determined.

Pimonidazole Based Measurements:

Hypoxic cells in the co-culture can be detected using the Hypoxyprobe-1Plus Kit (NPI Inc) according to the manufacturer's instructions. Inbrief, cells can be incubated with pimonidazole (400 μM) for 2 hrfollowed by fixation using 4% formaldehyde and permeabilized using 0.1%Triton X-100. After blocking with BSA, cells can be labeled withHypoxyprobe Mab1-FITC (1:200). Nuclei will be stained with Hoechstfollowed by fluorescence imaging.

pH Indicator Dye Based Measurements:

SNARF®-4F (Invitrogen, CA) which exhibits a significant pH-dependentemission shift (from yellow-orange to deep red fluorescence) allowsdetermination of hypoxic regions. The myocyte chamber can be injectedwith SNARF-4F (10 μM) and the resultant fluorescent intensity can beimaged.

The concentration of SNARF®-4F used (10 μM) is typical for monitoring pHgradients. However, in case the intensity levels are indistinguishablebetween the varying regions of the myocyte chamber, concentrations canbe dropped or increased to get better signal to noise ratio of the pHgradients. Other SNARF dyes such as SNARF-1 and SNARF-5 can be utilizedas needed.

Data can be measured by generation of a plot showing distinct gradientsof hypoxia (pH changes) from the capillary channel to the center of themyocyte chamber. A three zone differential pattern of ischemia isexpected with significant variations in the patterns following a lowischemia induced MI to a critical ischemia induced MI.

Biomarker Analysis in the Myocyte Chamber:

It is known that certain adhesion molecules such as ICAM-1 and Pselectin are upregulated following MI on the myocytes. In addition,hypoxia-inducible factor-1 (HIF-1) is known to be upregulated inmyocytes following hypoxic conditions. At regular time points of theischemia experiments (Table 1), cells can be incubated withfluorescently tagged antibodies to ICAM-1 and HIF-1. The entire chambercan be divided into virtual grids to yield areas with differentialexpression of these markers. The location of these markers on the cellscan be compared with the hypoxic regions from the SNARF assay tovalidate the zones of ischemia and the levels of biomarkers.

One can use antibodies to adhesion molecules (e.g. ICAM-1) to assess the% of cells expressing the inflammation marker and their location in theentire chamber. 2 μm fluorescent microspheres (Polysciences Inc.,Warrington, Pa.) at a concentration of 2×10⁸ particles/ml can be coatedwith anti-ICAM-1 (BD Biosciences, San Jose, Calif.). Microspheres washed2× in 0.1 M NaHCO3 buffer pH 9.2 can be incubated with Protein A (Zymed,Carlsbad, Calif.) at a concentration of 300 μg/ml and incubated at roomtemperature overnight to saturate the surface of the microsphere. Thefollowing day, a 2× wash with solution containing 1% BSA in HBSS can beperformed. The microspheres can be resuspended in 1% BSA in HBSS andincubated at room temperature for 20 minutes. Following incubation andsubsequent 2× wash with buffer, anti-ICAM-1 antibody at a concentrationof 100 μg/ml diluted in 1% BSA/HBSS can be mixed with the microspheres.Protein A binds the Fc fragment of the antibody to allow properorientation of the antibody. The microspheres can be held in thissolution at 4° C. until experimentation. Prior to experiments,microspheres can be washed twice with 1% BSA and HBSS. A control set ofmicrospheres with IgG coating can also be prepared. The preparedparticles can be injected into the myocyte chamber diluted in cellculture media to a concentration of 10⁶ particles/ml at the time pointshowing maximum MI. Following incubation period (e.g., 30 minutes), awash can be performed with PBS and the cells will be imaged.

Apoptotic Assays:

Cells under hypoxia are subject to stress eventually leading toapoptosis. Hence, they can be monitored using Tunnel (measurement ofnuclear DNA fragmentation), or Caspase (caspase activity in apoptoticcells) assay. Cells can be fixed with 4% paraformaldehyde for 1 hr andpermeabilized in 0.1% Triton-100, 0.1% sodium citrate (4° C. for 2 min)followed by incubation with TUNEL reaction mixture (1 hr at 37° C.).After washing, cells can be incubated with alkalinephosphatase-conjugated antibody (30 min at 37° C.) followed bycounterstained with hematoxylin. For Caspase assay, the cells can beincubated with the reaction solution (1 hr at 37° C.) followed by a washand counterstaining with Hoechst dye. We can also use Mitotracker red(stains mitochondria) for determining depolarization of cells followinghypoxia.

As before, the chamber can be divided into virtual grids to yield areaswith differential expression of the markers. The locations of thefluorescence images can be correlated with the SNARF and pimonidazoleimages to validate the hypoxia regions and zones of ischemia.

In addition, one can perform gene expression analysis (RT-PCR) tovalidate the upregulation of the hypoxia and inflammation markers.Finally, one can explore whole genome arrays to identify upregulatedgenes for the different regimes of ischemia.

Transport Model for Prediction of Hypoxia and Regeneration Following MI:

A morphologically realistic mathematical model of oxygen transport incardiac tissue following infarction can be used to supplement theexperimental studies. The model utilizes microvascular morphology ofcardiac tissue based on available morphometric images to simulateexperimentally measured oxygen levels after MI. Model simulations ofrelative oxygenation match experimental measurements closely and can beused to simulate distributions of oxygen concentration in normal andinfarcted hearts of rodents. 3,3-diheptyloxacarbocyanine iodide (DiOC7)and CD31 staining can be used to measure the number of anatomic andperfused vessels. Hypoxia levels can be measured by the use of EF5 (apentafluorinated derivative of etanidazole) that is preferentiallymetabolized in hypoxia cells.

Viability of Myocytes:

In order to assess the viability and healthy condition of the myocytesin the microfluidic device, one can use a combination of fluorescentdyes. Propidium iodide (Invitrogen, CA), an indicator of membraneleakiness and cell death in combination with SYTO16 (viable cellindicator) are commonly used to assess cell viability. Propidium iodideand SYTO16 at a concentration of 0.5 μg/mL in cell culture medium can beinjected into the myocyte chamber. After 15 minutes of incubation,images of the cells can be acquired using epi-fluorescence microscopy.The % of cells showing uptake of propidium iodide (stain in red) canindicate cells not in healthy condition, whereas cells staining withSYTO16 (stain green) indicate healthy cells. This method can be used toascertain % of viable cells following MI in the device.

One skilled in the art will appreciate that, for this and otherprocesses and methods disclosed herein, the functions performed in theprocesses and methods may be implemented in differing order.Furthermore, the outlined steps and operations are only provided asexamples, and some of the steps and operations may be optional, combinedinto fewer steps and operations, or expanded into additional steps andoperations without detracting from the essence of the disclosedembodiments.

The present disclosure is not to be limited in terms of the particularembodiments described in this application, which are intended asillustrations of various aspects. Many modifications and variations canbe made without departing from its spirit and scope, as will be apparentto those skilled in the art. Functionally equivalent methods andapparatuses within the scope of the disclosure, in addition to thoseenumerated herein, will be apparent to those skilled in the art from theforegoing descriptions. Such modifications and variations are intendedto fall within the scope of the appended claims. The present disclosureis to be limited only by the terms of the appended claims, along withthe full scope of equivalents to which such claims are entitled. It isto be understood that this disclosure is not limited to particularmethods, reagents, compounds compositions or biological systems, whichcan, of course, vary. It is also to be understood that the terminologyused herein is for the purpose of describing particular embodimentsonly, and is not intended to be limiting.

In one embodiment, the present methods can include aspects performed ona computing system. As such, the computing system can include a memorydevice that has the computer-executable instructions for performing themethod. The computer-executable instructions can be part of a computerprogram product that includes one or more algorithms for performing anyof the methods of any of the claims.

In one embodiment, any of the operations, processes, methods, or stepsdescribed herein can be implemented as computer-readable instructionsstored on a computer-readable medium. The computer-readable instructionscan be executed by a processor of a wide range of computing systems.

There is little distinction left between hardware and softwareimplementations of aspects of systems; the use of hardware or softwareis generally (but not always, in that in certain contexts the choicebetween hardware and software can become significant) a design choicerepresenting cost vs. efficiency tradeoffs. There are various vehiclesby which processes and/or systems and/or other technologies describedherein can be effected (e.g., hardware, software, and/or firmware), andthat the preferred vehicle will vary with the context in which theprocesses and/or systems and/or other technologies are deployed. Forexample, if an implementer determines that speed and accuracy areparamount, the implementer may opt for a mainly hardware and/or firmwarevehicle; if flexibility is paramount, the implementer may opt for amainly software implementation; or, yet again alternatively, theimplementer may opt for some combination of hardware, software, and/orfirmware.

With respect to the use of substantially any plural and/or singularterms herein, those having skill in the art can translate from theplural to the singular and/or from the singular to the plural as isappropriate to the context and/or application. The varioussingular/plural permutations may be expressly set forth herein for sakeof clarity.

It will be understood by those within the art that, in general, termsused herein, and especially in the appended claims (e.g., bodies of theappended claims) are generally intended as “open” terms (e.g., the term“including” should be interpreted as “including but not limited to,” theterm “having” should be interpreted as “having at least,” the term“includes” should be interpreted as “includes but is not limited to,”etc.). It will be further understood by those within the art that if aspecific number of an introduced claim recitation is intended, such anintent will be explicitly recited in the claim, and in the absence ofsuch recitation no such intent is present. For example, as an aid tounderstanding, the following appended claims may contain usage of theintroductory phrases “at least one” and “one or more” to introduce claimrecitations. However, the use of such phrases should not be construed toimply that the introduction of a claim recitation by the indefinitearticles “a” or “an” limits any particular claim containing suchintroduced claim recitation to embodiments containing only one suchrecitation, even when the same claim includes the introductory phrases“one or more” or “at least one” and indefinite articles such as “a” or“an” (e.g., “a” and/or “an” should be interpreted to mean “at least one”or “one or more”); the same holds true for the use of definite articlesused to introduce claim recitations. In addition, even if a specificnumber of an introduced claim recitation is explicitly recited, thoseskilled in the art will recognize that such recitation should beinterpreted to mean at least the recited number (e.g., the barerecitation of “two recitations,” without other modifiers, means at leasttwo recitations, or two or more recitations). Furthermore, in thoseinstances where a convention analogous to “at least one of A, B, and C,etc.” is used, in general such a construction is intended in the senseone having skill in the art would understand the convention (e.g., “asystem having at least one of A, B, and C” would include but not belimited to systems that have A alone, B alone, C alone, A and Btogether, A and C together, B and C together, and/or A, B, and Ctogether, etc.). In those instances where a convention analogous to “atleast one of A, B, or C, etc.” is used, in general such a constructionis intended in the sense one having skill in the art would understandthe convention (e.g., “a system having at least one of A, B, or C” wouldinclude but not be limited to systems that have A alone, B alone, Calone, A and B together, A and C together, B and C together, and/or A,B, and C together, etc.). It will be further understood by those withinthe art that virtually any disjunctive word and/or phrase presenting twoor more alternative terms, whether in the description, claims, ordrawings, should be understood to contemplate the possibilities ofincluding one of the terms, either of the terms, or both terms. Forexample, the phrase “A or B” will be understood to include thepossibilities of “A” or “B” or “A and B.”

In addition, where features or aspects of the disclosure are describedin terms of Markush groups, those skilled in the art will recognize thatthe disclosure is also thereby described in terms of any individualmember or subgroup of members of the Markush group.

As will be understood by one skilled in the art, for any and allpurposes, such as in terms of providing a written description, allranges disclosed herein also encompass any and all possible subrangesand combinations of subranges thereof. Any listed range can be easilyrecognized as sufficiently describing and enabling the same range beingbroken down into at least equal halves, thirds, quarters, fifths,tenths, etc. As a non-limiting example, each range discussed herein canbe readily broken down into a lower third, middle third and upper third,etc. As will also be understood by one skilled in the art all languagesuch as “up to,” “at least,” and the like include the number recited andrefer to ranges which can be subsequently broken down into subranges asdiscussed above. Finally, as will be understood by one skilled in theart, a range includes each individual member. Thus, for example, a grouphaving 1-3 cells refers to groups having 1, 2, or 3 cells. Similarly, agroup having 1-5 cells refers to groups having 1, 2, 3, 4, or 5 cells,and so forth.

From the foregoing, it will be appreciated that various embodiments ofthe present disclosure have been described herein for purposes ofillustration, and that various modifications may be made withoutdeparting from the scope and spirit of the present disclosure.Accordingly, the various embodiments disclosed herein are not intendedto be limiting, with the true scope and spirit being indicated by thefollowing claims.

All references recited herein are incorporated herein by specificreference in their entirety.

This patent document incorporates by specific reference in theirentirety the following patents and patent applications: U.S. Pat. No.7,725,267; U.S. Pat. No. 8,355,876; U.S. Pat. No. 8,175,814; U.S. Pat.No. 8,380,443; U.S. Pat. No. 8,417,465; U.S. Pat. No. 8,589,083; U.S.2010/0227312; PCT/US2013/072081; U.S. 2013/0101991; and U.S.2013/0149735. These applications provide background and state of the artas well as definitions for terms of art.

This patent document incorporates by specific reference in theirentirety co-filed applications that claim priority to the sameprovisional application 61/775,158 filed Mar. 8, 2013, which co-filedapplications include: C1478.10020US02 (Attorney's authorized to includeserial number once known); C1478.10020US03 (Attorney's authorized toinclude serial number once known); and C1478.10020US04 (Attorney'sauthorized to include serial number once known).

1. A cell culture device comprising: an internal chamber configured foran internal cell culture that has at least one port coupled to aperfusion modulating system capable of modulating perfusion in theinternal chamber; at least one fluid channel bordering the internalchamber that is configured for a channel cell culture that has at leastone port coupled to the perfusion modulating system capable ofmodulating perfusion in the fluid channel; and a wall separating theinternal chamber and at least one fluid channel having gaps that fluidlycouple the internal chamber with the at least one fluid channel, whereinthe perfusion modulating system causes reduced fluid flow in theinternal chamber and/or at least one fluid channel.
 2. The cell culturedevice of claim 1, wherein the perfusion modulating system includes apump.
 3. The cell culture device of claim 2, wherein the internalchamber includes a first cell type and the at least one fluid channelincludes a second cell type.
 4. The cell culture device of claim 3,wherein the first cell type has an ischemic zone in the middle, anon-ischemic zone adjacent with the at least one fluid channel, and aborder zone between the ischemic zone and non-ischemic zone
 5. The cellculture device of claim 1, wherein the internal chamber and at least onefluid channel are modeled from physiological features.
 6. The cellculture device of claim 1, wherein the internal chamber and at least onefluid channel are modeled from idealized features.
 7. A cell culturesystem comprising: the device of claim 1; and the perfusion modulatingsystem coupled to the port of the internal chamber and/or to the port ofthe at least one fluidic channel.
 8. A method of inducing ischemia, themethod comprising: providing the device of claim 1 having a first cellculture in the internal chamber and a second cell culture in the atleast one fluid channel; modulating perfusion in the internal chamberwith the perfusion modulating device; and assaying for ischemia in thefirst cell culture.
 9. The method of claim 8, comprising: modulatingperfusion in the at least one fluid channel.
 10. The method of claim 8,comprising varying flow rate and duration of fluid flow in the at leastone fluid channel so as to vary perfusion in the internal chamber. 11.The method of claim 8, comprising introducing a chemical, biologicaland/or physical insult to the first cell culture in the internalchamber.
 12. The method of claim 8, comprising inducing gradients ofhypoxia in the internal chamber.
 13. The method of claim 8, comprisinginducing hypoxia in tissue cells (e.g. myocytes, neurons, nephrons, orhepatocytes) in the internal chamber.
 14. The method of claim 8,comprising screening therapeutics on hypoxic cells in the first cellculture in the internal chamber.
 15. The method of claim 8, comprisingcharacterizing viability, pH, hypoxia, or biomarkers in cells in thefirst cell culture in the internal chamber.
 16. The method of claim 8,comprising regenerating cells the internal chamber.
 17. The method ofclaim 8, comprising visualizing cells in the first cell culture in theinternal chamber.
 18. The method of claim 8, comprising simulating amyocardial infarct in the first cell culture of myocytes in the internalchamber.
 19. The method of claim 8, comprising modulating nutrientlevels in the internal chamber sufficient to induce varying (low,moderate, high) levels of ischemia.
 20. The method of claim 19,comprising modulating nutrient levels in the internal chamber and atleast one fluid channel sufficient to induced moderate to severeischemia.